Multilayer conductive appliance having wound healing and analgesic properties

ABSTRACT

A dressing for promoting healing and pain relief of the body of a living organism having a pathologic condition has at least one layer of conductive material having a resistance no greater than 1000 Ω/cm 2 . When placed proximate a portion of the body of the living organism suffering from the pathologic condition, the dressing alters the electrodynamic processes occurring in conjunction with said pathologic condition to promote healing and pain relief in the living organism. When used as a wound dressing, the conductive material is placed in contact with tissue around the periphery of the wound and with the wound, lowering the electrical potential and resistance of the wound and increasing the wound current. In an exemplary embodiment, the conductive material is a multi-ply nylon fabric plated with silver by an autocatalytic electroless plating process and with the plies in electrical continuity. The dressing provides an antimicrobial and analgesic effect. The dressing may be provided for numerous applications and may include other layers such as an absorbent layer, a semi-permeable layer and additional layer of conductor material. Multilaminate embodiments of the present invention exhibit conductive material concentration gradients and, potentially, a capacitive effect when sequential conductor layers are insulated by intervening layers.

CROSS-REFERENCE TO RELATED APPLICATION

This application is a Continuation of prior International ApplicationSerial No. PCT/US98/19689 filed on Sep. 22, 1998, which claims priorityto U.S. Pat. No. 6,087,549 issued Jul. 11, 2000.

TECHNICAL FIELD OF THE INVENTION

The present invention relates to wound dressings and medical devices forrestoring the premorbid electro-biological activity of tissue systemsthat are altered by pathological conditions in the animal and humanbody. More particularly, it relates to metalized dressings and medicaldevices that enhance tissue healing and reduce the perception of pain byinfluencing in a passive (non energy requiring) manner the electricalparameters of the injured tissue and that may also exhibit antibacterialand antifungal efficacy.

BACKGROUND ART

Wound treatment has become a more highly developed area of scientificand commercial investigation as new research has revealed the workingsof the healing process. More rapid healing of a wound reduces long termhealthcare costs and improves patient recovery, including regaining ofsensation, function and aesthetics.

Healing, like all other biological processes, is a cellular process. Theoccurrence of an injury immediately triggers the onset of this process,which continues until the injury is healed. Although its exact mode ofaction is not yet understood, it is clear that a feedback mechanismmonitors the extent of tissue damage and adjusts cellular activity inthe injured area to produce the exact amount of healing needed.

As used herein, the terms ‘wound” and “injury’ refer to tissue damage orloss of any kind, including but not limited to, cuts, incisions(including surgical incisions), abrasions, lacerations, fractures,contusions, burns, amputations and the like.

Healing in general is known to be related to the degree of the injury,and the electrical potential difference between the site and surroundingintact tissue. In particular, regeneration in amphibians such assalamanders and fracture healing in mammals are associated with complexchanges in the local DC (direct current) electric field. The electricfield gradually returns to normal, pre-injury levels as the injuryheals. Conversely, failure of the normal healing process, as in fracturenonunions, is associated with the absence of appropriate electricalsignals at the site of the injury.

More particularly, and by way of example, healthy human skin exhibits anelectrical potential across the epithelium, i.e., the transepithelialpotential (TEP or epidermal battery). The TEP is generated by an activeionic transfer system. Sodium ions enter the outer cells of theepithelium via specific channels in the outer membrane of these cellsand migrate along a steep electrochemical gradient. Through a series ofelectrogenic pumps that actively pump sodium ions and tight gapjunctions between epithelial cells that do not allow the reverse passageof the sodium ions, the epidermal battery is generated. This results ina transport of sodium ions from the water bathing the epithelium to theinternal body fluids of the animal, and the generation of a potential ofthe order of 10 mV to 70 mV across the epithelium.

While the general topic of wound healing has an extensive and broadliterature base with excellent review papers written by Eaglstein 1984,and Eckersley and Dudley 1988, published research on the role ofgenerated electrical potentials in the healing process has been limited.

Notwithstanding, the existence of wound currents has been recognized formore than 200 years. In early experiments, about 1 μA of current wasfound to leave a wound in human skin immersed in saline (Barker 1982,Jaffe 1984). In 1980, lllingworth and Barker measured currents withdensities of from 10-30 μA/cm² leaving the stump surface of children'sfingers whose tips had been accidently amputated. This outflowing ofcurrent has also been called the “Current of Injury”. It is generallyrecognized that the electromotive force (EMF) driving currents fromwounds made in skin is a direct result of disruption of thetransepithelial potential (TEP). It is generally believed that ioniccurrents primarily generated by the epithelium's electrogenic sodiumtransport mechanism are responsible for the TEPlkk (epidermal battery).Founds and Barker (1983) recorded the TEP of human skin with valuesranging from about minus 10 mV to almost minus 60 mV depending on theregion measured. Barker (1982) reported that interruption of the sodiumtransport system by a blocking agent called amiloride, resulted in areduced TEP. When amiloride is added to areas of wounding such as alaceration, the TEP is reduced to about one half its original value andthe healing process was significantly slowed.

Borgens (1982) has reported that trauma or tissue damage disrupts thenormal electrical pattern of the cell, tissue, or organism. It isbelieved that the altered electrical profile serves as a signal for or acausative agent in the repair or regenerative process.

Barker (1982) recognized that when a wound is made in the skin, anelectric leak is produced that short-circuits the TEP (epidermalbattery) allowing the voltage to reverse at the wound surface. With thedisruption of the epithelium's electrogenic sodium transport mechanismwithin the wound, the TEP on the surface of the wound is significantlyaltered in the reverse direction. As one progresses laterally from thewound surface to normal tissue surrounding the wound, the potentialacross the skin is found to increase, until a point is reached at whichthe potential across the skin is the full value normally found inunwounded skin. Thus a lateral voltage gradient is generated in theproximity of the wound margin as one transitions from wounded tissue tonormal tissue. Jaffe and Vanable (1984) have reported the lateralvoltage gradient in experimental animals could be as high as 140 mV/mm.It has also been reported that within 24 hours after a wound, theepidermally generated lateral voltage drops by 95%. Therefore, it isrecognized that there is a lateral voltage gradient or “lateralpotential” in the epidermis close to the margin of a wound. The greatestepidermally generated lateral voltage is found in the region of highesttissue resistance. In the amphibian, the locus of the major lateralpotential is at the high resistance space between the epidermis and thedermis; whereas, in the mammal, the locus of the major lateral potentialis at the space between the living and the dead comified layers ofepithelium.

The role that endogenous electric fields play in bone physiology and therepair process is well documented in the medical literature. Friedenbergand Brighton first reported in 1966 that a peak of electronegativityoccurred at a fracture site, along with a general electronegativity ofthe entire bone, when referred to the proximal epiphysis. They alsonoted peaks of electronegativity were measured on the skin over tibialfractures in both rabbits and humans.

There have been numerous studies conducted on the wound healing ofamphibians due to the phenomenon of tissue regeneration by amphibiansand because the rate of wound healing is significantly greater inamphibians than in mammals.

Winter (1964) reported that wound healing in mammalian skin occurs overdays or even weeks, with epithelial cell migration rates ranging from 7(dry wound) to 20 (wet wound) micrometers/hour. Amphibian skin woundsheal within hours, with epithelial cell migration rates ranging from 60to more than 600 micrometers/hr. The difference in the rates of healingof mammalian skin and amphibian may be partially explained byenvironmental factors. More specifically, the aqueous environment of anamphibian bathes the outer surface of the epithelium and the deadcornified layer is thin and moist. As a result, the cornified layer isnot a significant barrier to the movement of sodium ions into theepidermal cells. In contrast, the dead, cornified layer of mammalianskin is thick and dry, representing a significant barrier to themovement of sodium ions into the epidermal cells. It is generallyrecognized that dry wounds (as in mammals) heal more slowly than woundsthat are kept moist by occlusive dressings. Keeping the epidermissurrounding a wound and the wound itself moist stimulates the wound toclose.

In summary, it has been recognized that keeping wounds moist maysimulate an environment like that which exists in amphibian healing andaccelerating the mammalian healing process. U.S. Pat. No. 5,512,041 ofBogart teaches a wound dressing that promotes moist wound healingcomprising a backing sheet coated with a pressure sensitive adhesive, anabsorbent pad and a net extending across the pad and attached to theadhesive.

Besides the effect of moisture on wound healing, microbial growth at thesite of injury has a great effect on healing time, with low bacterialcounts (less than 10² to 10³) promoting healing. While there are scoresof antibacterial and antifungal agents, the efficacy of silver is ofparticular interest herein. The antimicrobial and antifungal propertiesof silver and silver compounds are well known. Topical preparations thatcontain silver or silver compounds—silver nitrate solution, silversulfadiazine cream, colloidal silver compositions, silver-proteincompounds such as Argyrol, and so forth, have been and some are widelyused in medicine. The useful effects of these compositions are due tothe small amounts of free silver ions produced by dissociation of thesilver moiety from the compound to form ionic silver.

The effectiveness of silver as an antimicrobial agent is at least partlydetermined by the delivery system. Most silver compounds that dissociatereadily (silver nitrate) and produce large numbers of free silver ionsare highly toxic to mammalian (including human) tissues. Less-toxiccompounds, including silver sulfadiazine cream (widely used in thetreatment of burns) do not dissociate readily and therefore do notrelease large numbers of silver ions. These compounds must be re-appliedfrequently to maintain their clinical efficacy.

Silver and other metals have been reported to be used in wound dressingsand materials therefor. Antimicrobial activity may be achieved by puremetals, metal salts, metal organic compounds or combinations of metalsto create a galvanic cell reaction. Fabo (U.S. Pat. No. 5,340,363)discloses a dressing that includes an outer absorbent layer and an innerporous, hydrophobic layer knitted of elastic threads and encapsulated bya soft, hydrophobic silicone or polyurethane gel. The gel can be used asa carrier for antibacterial agents such as zinc, pain-relievingsubstances, and agents that stimulate wound repair. Klippel et al. (U.S.Pat. No. 3,830,908) use micronized allantoin as a carrier for abactericidal or bacteriostatic ingredient (such as silver citroallantoinate) that is dispersed on the surface of a plastic air splintor other bandaging product. This material depends on the separation ofthe molecular moieties to provide the antibacterial action.

McKnight et al. (U.S. Pat. No. 3,800,792) disclose a surgical dressinghaving a layer of tanned, reconstituted collagen foam film laminated toa thick, continuous layer of an inert polymer. The collagen layercontains finely-divided silver metal added by soaking the collagen filmin Tollen's reagent. Stowasser (U.S. Pat. No. 2,934,066) makes adressing of absorbent metal-coated fibers, such as a carding fleececoated with aluminum and backed by compressed cellulose, and polyamidefibers coated with vacuum-deposited silver.

U.S. Pat. No. 5,782,788 of Widemire teaches that a layer of silver foilaffixed to a gauze pad inhibits the growth of bacteria, viruses, andfungi by providing a source of silver ions that are driven off the foilby the negative DC field of the body.

U.S. Pat. Nos. 5,454,886, 5,681,575, and 5,770,255 to Burrell teaches avapour deposition technique for the purpose of a sustained release ofmetal ions sufficient to produce an anti-microbial effect. U.S. Pat. No.5,695,857 to Burrell teaches an active antimicrobial surface thatcomprises a film consisting of at least an antimicrobial element andanother electrochemically nobler element and forms a multilayer galvaniccell for releasing the antimicrobial element at the surface.

Dressings for provision of electrical stimulation are also known. Forexample, Jones (U.S. Pat. No. 4,911,688) covers a wound with a clearcover that serves as a hollow chamber for holding a fluid such as salinein contact with a wound. When connected to a voltage source, a metalanode and a return electrode create free ions and an electrical field toenhance healing and tissue regeneration. Juhasz (U.S. Pat. No.4,817,594) discloses a multi-layer dressing for covering discharging,malodorous wounds. The dressing includes an open mesh layer of anelectrically-conductive material such as silver and a layer of charcoalfabric. Seiderman (U.S. Pat. No. 4,767,401) teaches a bandage-likedevice used for iontophoretic administration of medicaments, includingsilver-protein colloids. The device includes a metal foil electrode(preferably aluminum), and makes use of the slight inherent negativeelectric charge proximate a wound site to generate a small electricfield at the site.

Matson (U.S. Pat. No. 4,728,323) coats a substrate (nylon fabric,polymeric film, fiberglass, gauze or polyurethane foam) with a film of asilver salt, e.g., silver chloride or silver sulfate deposited by vaporor sputter coating techniques to provide an antimicrobial effect.Alternatively, fibers can be coated and then woven or knitted into afabric. Other silver salts referred to in this patent are silverbromide, silver fluoride, silver chloride, silver nitrate, silversulfate, silver alkylcarboxylate, silver sulphadiazine, and silverarylsulfonate. In the dry crystalline form these salts deposited as thinfilms are diaelectric materials with extremely poor conductivity. Whenthe crystalline salts are immersed in physiological solutions theycontinue to exhibit their dielectric characteristics. Konikoff (U.S.Pat. No. 4,142,521) shows a bandage or surgical sponge materialincorporating one or more electret elements, each electret providing asmall electrostatic field to the area of the wound.

Spadaro (1974) and Becker (1976) reported electrically-generated silverions, could can penetrate deeply into the tissues, were noted to beeffective even against antibiotic-resistant strains of bacteria, fungi,etc., inhibiting growth in vivo and in vitro at current densities as lowas 10 μA/mm² and silver ion concentrations as low as 0.5 mg/ml. U.S.Pat. No. 4,528,265 of Becker discloses processes and products thatinvolve subjecting mammalian cells to the influence ofelectrically-generated silver ions. Anodic silver causes cells such asmammalian fibroblasts to assume a simpler, relatively unspecialized formand to resemble dedifferentiated or embryonic cell types. Aniontophoretic system for promoting tissue healing processes and inducingregeneration is described in Becker et al., U.S. Pat. application Ser.No. 08/623,046, filed Mar. 28, 1996. The system is implemented byplacing a flexible, silver-containing anode in contact with the wound,placing a cathode or intact skin near the anode, and applying awound-specific DC voltage between the anode and the cathode.Electrically-generated silver ions from the anode penetrate into theadjacent tissues and undergo a sequence of reactions leading toformation of a silver-collagen complex. This complex acts as abiological inducer to cause the formation in vivo of an adequateblastema to support regeneration. The above systems have limitations inthat either an electrolyte or an external voltage source is required.

Seiderman U.S. Pat. No. 4,034,750 teaches that an electrochemicallyactive ostonic collagen paste capable of generating a galvanic currenthas the property of electrochemically-linking collagen fibrils to forman adherent skin-like protective membrane. Seiderman notes that when a10% isotonic collagen paste is applied locally over a wound that anelectric field is established between the collagen paste dispersion andthe animal body; the paste will exhibit an overall positive charge whilethe areas surrounding the wound site will exhibit an effective negativeelectrical potential. It is generally recognized by those skilled in theart that mammalian wounds without treatment or 10% isotonic collagenpaste are more positive than the surrounding tissue that will exhibit aneffective negative electrical potential.

Regardless of whether silver is provided in the form of silver ions oras a topical composition (silver nitrate solution, silver sulfadiazinecream, or the like), its beneficial effects are manifested primarily atthe treated surface and immediately adjacent tissues, and are limited bythe achievable tissue concentration of silver ions. Despite theavailability of numerous techniques for the delivery of silver andsilver compounds in vitro and in vivo, there remains a need for adelivery system that is capable of supplying clinically usefulconcentrations of silver ions to a treatment site without the need foradjuvant electrical stimulation.

In addition to the foregoing therapeutic strategies, metals have beenused to achieve diverse beneficial effects.

U.S. Pat. No. 2,577,945 of Atherton teaches a metallic film for thepurpose of providing a heat-reflective surface, touching the body orraised off the body. The heat reflective surface would conserve the heatfrom the wound and thereby assist with wound healing.

U.S. Pat. No. 3,326,213 of Gallaher teaches the application of anelectrostatically charged gold leaf film from 0.0003 to 0.1 mil thick totreat damaged mammalian tissue and arrest hemorrhaging vasculature. Theelectrostatic charge allows the gold leaf to cling to the body tissue.

U.S. Pat. No. 3,420,233 of Kanof teaches application of gold leaf tostimulate epithelialization of an avascular ulcer. An electrostaticdifferential between the gold leaf and the ulcer is achieved by applyethyl alcohol to the ulcer.

U.S. Pat. No. 4,297,995 of Golub teaches a metal foil or a metalfoil-polyester laminate forming a base plate provides a suitable barriermaterial for a bandage that can dispense medications.

U.S. Pat. No. 5,374,283 of Flick teaches an electrical apparatus for thetreatment of body pain and edema by delivering an electricalsignal/voltage.

U.S. Pat. No. 4,619,252 of Ibboott teaches a therapeutic method andtherapeutic means for applying a voltage to the human body by asheetlike battery utilizing a negative electrode composed of a metalfoil such as aluminum or zinc.

In reviewing prior art, metal coatings on wound dressings have been usedfor: (1 thermal activity; (2) for arresting hemorrhaging vasculature;(3) for stimulating wound healing; (4) for a barrier material; (5) fordelivery of electrical signals as in the form of an electrode (6) forpart of a battery to apply voltage to the human body (7) forantimicrobial activity and (8) for cell modification. The prior art doesnot teach altering a wound's electrical parameters with a passive,highly conductive element.

The prior art does not address the restoration of a homeostaticelectromagnetic field environment for wounded tissue nor the alterationof wound currents that accelerate healing. Accordingly, it is an objectof the present invention to provide wound dressings and apparatus whichcan promote healing, stimulate cell growth, and alleviate pain throughelectrically conductive elements.

DISCLOSURE OF THE INVENTION

A dressing for promoting healing and pain relief of the body of a livingorganism having a pathologic condition has at least one layer ofconductive material with a resistance no greater than 1000 Ω/cm². Whenplaced proximate a portion of the body of the living organism sufferingfrom the pathologic condition, the dressing alters the electrodynamicprocesses occurring in conjunction with the pathologic condition topromote healing and pain relief. When used as a wound dressing, theconductive material is placed in contact with healthy tissue around theperiphery of the wound and with the wound. In an exemplary embodiment,the conductive material is a multi-ply nylon fabric coated with silverand with the plies in electrical continuity. Alternative embodiments mayinclude other layers such as an absorbent layer, a semi-permeable layerand additional layers of conductor material. Multilaminate embodimentsof the present invention exhibit conductive material concentrationgradients and, when sequential conductor layers are insulated byintervening layers, a capacitive effect.

BRIEF DESCRIPTION OF THE DRAWINGS

The invention is illustrated in the drawings in which like referencecharacters designate the same or similar parts throughout the figures ofwhich:

FIG. 1 is a schematic cross-sectional view of the laminate structure ofa first embodiment of the present invention;

FIG. 1A is a schematic cross-sectional view of a second embodiment ofthe present invention showing a gradient of silver fiber concentrationin the material, as depicted by a varying stippling density;

FIG. 2 is a schematic cross-sectional view of the laminate structure ofa third embodiment of the present invention;

FIG. 3 is a schematic perspective view of a dressing according to afourth embodiment of the present invention for use around an externalfixature pin structure;

FIGS. 4A-C are schematic perspective views of a dressing.

FIG. 4 is a schematic perspective view of a dressing according to afifth embodiment of the present invention for use around a pin extendingfrom the skin;

FIG. 5 is a schematic plan view of a dressing according to a sixthembodiment of the present invention for use at an ostomy site;

FIG. 6 is a schematic plan view of a dressing according to a seventhembodiment of the present invention for use at a tracheostomy site;

FIG. 7A is a schematic plan view of a dressing according to an eighthembodiment of the present invention for use at an i.v. catheter site;

FIG. 7B is a schematic side view of a dressing according to FIG. 7A insitu;

FIG. 8 is a schematic view of a dressing according to a ninth embodimentof the present invention for use with a urinary catheter;

FIGS. 9-12 are graphs of the experimental data pertaining to themicrobial inhibition zone achieved in cultures of several organisms byvarious materials, including a material in accordance with the presentinvention.

FIG. 9 shows the data using P.aeruginosa depicted in FIG. 16.

FIG. 10 shows the data using E.coli depicted in FIG. 14.

FIG. 11 shows the data using E.faecalis depicted in FIG. 15

FIG. 12 shows the data using S.aureus depicted in FIG. 13.

FIGS. 13-16 are photographs of different Petri dishes containing thelabeled bacteria, showing the zones of inhibition that form the basisfor FIGS. 9-12;

FIGS. 17 and 18 are antibiotic resistant bacteria showing excellentzones of inhibition;

FIGS. 19-24 are photographs of a wound of a patient designated “LS” astaken over a span of several months and showing the healing of the woundtreated with a dressing in accordance with the present invention.

FIGS. 25-29 are photographs of a wound of a patient designated “JL” astaken over a span of several months and showing the healing of the woundtreated with a dressing in accordance with the present invention;

FIG. 30 is a schematic depiction of a cross-section of wounded mammalianskin with a dressing in accordance with a tenth embodiment of thepresent invention positioned over the wounded area;

FIG. 31 is a graph of voltage verses position on the wounded skin asshown in FIG. 30;

FIG. 32-35 show various laminar structures associated with elevenththrough fourteenth embodiments of the present invention;

FIG. 36 shows a fifteenth embodiment of the present invention with thelaminar dressing formed into a configuration for packing body cavities;

FIG. 37 shows a sixteenth embodiment of the present invention forpacking a body cavity;

FIG. 38 is a schematic cross-sectional view of a seventeenth embodimentof the present invention for covering and treating a tooth andsurrounding gum;

FIG. 39 is an elevational view of an eighteenth embodiment of thepresent invention wherein the laminar material of the present inventionis formed into a tube shape;

FIG. 40 is a schematic perspective view of a nineteenth embodiment ofthe present invention involving the application of the laminar materialof the present invention to the gingival tissue on the buccal surface;

FIG. 41 is a diagrammatic cross-sectional view of the conductive layerin accordance with a twentieth embodiment of the present invention;

FIG. 42 shows a perspective view of a twenty-first embodiment of thepresent invention wherein the multi laminate material of the presentinvention is formed into a glove;

FIG. 43 is a schematic perspective view of a twenty-second embodiment ofthe present invention wherein a tubular wound drain is formed from themultilaminate material of the present invention;

FIG. 44 is a perspective view of a twenty-third embodiment of thepresent invention wherein the multilaminate material is formed into afoot orthotic; and

FIG. 45 is a perspective view of a knee sleeve formed from the materialof the present invention.

BEST MODE FOR CARRYING OUT THE INVENTION

The present invention encompasses a wound dressing and/or appliancehaving a highly electrically conductive layer. The highly conductivelayer in and of itself has inventive aspects in the identification ofits functionality, its formation and use. The highly conductive layermay be used in combination with other dressing layers. In describing thepresent invention, the multilaminate composite shall be described firstfollowed by a description of the form and function of the highlyconductive layer.

Referring to FIG. 1, a first embodiment of the present inventionincludes a laminate structure 10 composed of at least two layers that isapplied to a body surface such as the skin 5. In the embodiment shown,three layers of material 14, 16 and 18, are utilized. Any number oflayers could be utilized depending on the composition, thickness,denier, fiber density and other characteristics of the material. Thereare also practical limits on the number of layers of material usable,such as cost or material bulk which begin to outweigh the incrementalbenefits of an additional layer.

Each layer 14, 16 and 18 is a flexible material preferably composed of amixture of silvered fibers and nonmetalized fibers. The silver ispreferably of high purity, preferably from about 99.0% to about 99.9%,although lower purity levels can function in the present invention. Highpurity reduces the likelihood that contaminants or undesirable ions maycontact or penetrate the wound or skin. The base fiber is preferablynylon, although other polymers or materials can be used with the presentinvention. The most important qualities of the base fiber are that itmust be flexible and it must be capable of being coated with a metal ormetals. The base fiber may be the same as the non-metallized fibers.

Each of the base fibers is completely coated with metallic silver by anautocatalytic e lectroless plating process. The thickness of the uniformcoating varies from 0.2 micrometers to 1.0 micrometer. The thickness ofcoating is reported in the percentage of weight of silver plated to theweight of the fabric without silver plating. The amount of coating mayvary from about 5% to about 40% by weight, more preferably about 15% byweight.

The silver fibers are commercially available from Omnishied, Inc.,Clarks Summit, Pa., Swift Metalizing Corp., Hartford, Conn., andSauquoit Industries, Inc., Scranton, Pa. The denier of the silver fibersis in the range of from about 1 denier to about 120 denier, morepreferably of from about 3 denier to about 80 denier, and still morepreferably about 3 denier to 24 denier.

The base fiber is preferably a flexible material, such as, but notlimited to, acetate, flax, glass, modacrylic, olefin polyester andpolyethylenes, rubber, saran, spandex, vinyl, vinyon, cotton, wool, silkor other natural fiber, rayon, nylon, glasswool, acrylic, syntheticpolymers, such as polyolefins sold under the trademarks DELNET, andSTRINGNET, other synthetic materials, blends or multicomponent fibers,either woven or nonwoven. The material chosen should be flexible,nonconductive, preferably biologically inert, flexible nonconductive andalso preferably nonimmunogenic. Since some individuals may have atopical hypersensitivity to certain fiber materials, the base fiber ispreferably nonallergenic or hypoallergenic. Preferred base fibers arenylon, rayon, glass, silk, polyolefin or cotton. It is to be understoodthat other fiber materials can be used to achieve the objects of thepresent invention.

In a first embodiment, the silver fibers and nonmetalized fibers aregenerally equally distributed throughout each layer 14, 16, 18 of thematerial. For example, the silvered fibers may be mixed with thenonmetalized fibers by air to create a random, generally uniform mixtureof fibers. Alternatively, it is contemplated as being within the scopeof the present invention to have areas of different fiber distributionfor certain applications. FIG. 1A shows an alternative embodimentwherein one portion 14A, 16A or 18A of layers 14, 16, 18 has a higheraverage concentration or density of metalized fibers than a secondportion 14B, 16B or 18B. Gradient concentration of mixed fibers can bemade according to processes known to those of ordinary skill in the art.An application of a controlled fiber distribution is for a body cavityarea dressing, such as, but not limited to, a vaginal or rectal areadressing. The mucosal tissue of such body cavities as the vagina andrectum require much lower percentage concentrations of silver fibersthan epithelial tissue such as skin.

The ratio of silvered fibers to nonmetalized fibers is an importantaspect of the present invention. In a given layer, the ratio of silverfibers to nonmetalized fibers can be from about 1:100 to about 1:1 morepreferably from about 1:50 to about 1:2, and still more preferably fromabout 1:20 to about 1:4. Where the layers are 100% silver nylon, theratio would be about 1:0. The layers of material are arranged so thatthe layer which will be in contact with the body, e.g., a wound site orvaginal wall, has the highest ratio, with a layer next removed from thewound site having a lower ratio, and so forth. Thus, there is adecreasing concentration gradient of silvered fibers in subsequentlayers 14,16,18 further from the wound site.

In addition to a decreasing concentration gradient, the thickness of thelayers preferably, although not mandatorily, increases as the distancefrom the body, e.g, skin, increases; i.e., the thickness of the layer 14next to the skin 5 is preferably less than the thickness of the layer 16and 18 farther from the skin.

The layers 14, 16 and 18 can be laminated by sonic welding, adhesives,heated calendar rolls, needle punching, hydraulic needling or otherfiber layer laminating or joining processes known to those of ordinaryskill in the art. In a needle punching process, the layers aresuperimposed and passed through a pair of niprolls, one of the niprollshaving series of spaced apart pins, needles or other protrusionsextending radially therefrom, and the other niproll being smooth. Thepins enter the fabric layers 14, 16, 18 and push fibers from one layerinto another layer, creating a physical bonding between the layers.After passing through the niproll assembly, the laminate structure canbe wound up on a take up roll or further processed.

The laminate structure 10 is semipermeable to most substances. A layermay be added that would function as a semiocclusive membrane permittinggas exchange but retarding the rate of water loss. Moisture retention ofthe structure 10 keeps the wound site moist to promote healing.Preferably, the structure 10 has a permeability to water vapor fromabout 500 grams/square meter/24 hours to about 3000 grams/squaremeter/24 hours.

In an alternative embodiment, shown in FIG. 2, a laminate structure 20is comprised of layers 24, 26 and 28 of the mixed silveredfiber/nonsilvered fiber material like that of layers 14, 16, 18 of FIG.1. Between each layer 24, 26, 28 is a layer of a nonconducting flexiblematerial 22 that can be any flexible, porous material that isimmunogenically inert and semipermeable. Such materials include, but arenot limited to acetate, flax, glass, modacrylic, olefin polyester andpolyethylenes, rubber, saran, spandex, vinyl, vinyon, cotton, wool, silkor other natural fiber, rayon, nylon, glasswool, acrylic, syntheticpolymers, such as, polyolefins sold under the trademarks DELNET, andSTRINGNET, other synthetic materials, blends or multicomponent fibers,either woven or nonwoven. A preferred material is DelNet®, a highdensity polyethylene blend available from Applied ExtrusionTechnologies, Inc., Middletown, Delaware. The use of the alternatinglayers 24, 26, 28 of silver-containing material and nonsilvered layers22 creates a capacitor-like laminate, as will be described in greaterdetail hereinbelow.

The present invention as described above is primarily usable as adressing to promote wound healing. The present invention also is usableas an antibacterial and antifungal. Surprisingly, the present inventionalso appears to have analgesic properties. The anticipated mode ofoperation of the present invention shall be described more fully below.Prior to such description, additional examples of the present inventionshall be described.

The laminate structure 10 or 20 of the present invention can be formedinto any of a number of possible shapes, patterns or

Geometrics, depending on the application and topography of the wound orapplication site. Several examples are shown in FIGS. 3-8. FIG. 3 showsa dressing 30 with a composition like that of structures 10 or 20 havinga plurality of slits 52 for accommodating a set of fixature pins 54 thatextend through the skin 5 and which are joined by cross bar 56. Thedressing 50 is appropriate for use in maintaining an antimicrobialenvironment, reducing pain and inducing healing.

FIG. 4A shows a sleeve 60 made from laminate material 10 or 20 rolledinto a cylinder for placement over a pin 72, such as would be used forexternal orthopaedic fixation devices.

FIG. 5 shows a dressing 70 constructed of material 10 or 20 with acircular slit 72, usable as a dressing for an ostomy surgical site, orin conjunction with a feeding tube (not shown).

FIG. 6 shows a dressing 80 formed from material 10 or 20 with a circularopening 82, usable as a dressing for a tracheostomy surgical site.

FIG. 7A shows a dressing 90, similar to dressing 80, but with a smalleropening or a cross slit forming an “x” 92, usable in conjunction with ani.v. catheter.

FIG. 7B shows a catheter 94, inserted through the skin 5 to vein 96. Thedressing 90 is placed around the catheter 94.

FIG. 8 shows a cup-shaped dressing 100 made from material 10 or 20,usable with a urinary catheter 102. The dressing 100 is fitted over thehead of a penis 104 and taped or otherwise attached to the catheter 102.

The present invention can also be used as or in conjunction with anexternal post-labor and delivery vaginal pad, such as after anepisiotomy, or, standard surgical incision. The embodiment is intendedfor abrasions, lacerations, puncture wounds, partial and full thicknessburns, skin tears, traumatic amputations, and dermal ulcerations(vascular, venus, pressure, and diabetic).

The present invention can also be used as a wound drain, where thedressing is a layering of silver containing layers (100% silver-coatednylon fibers) alternating with a nonconductive material, such as, butnot limited to, DelNet®. The layering can be two silver platednylon/nylon, between which is sandwiched a layer of DelNet®. A wounddrain preferably has silver coated fiber on both outer surfaces with alayer of nonconducting nylon, polyolefins, rayon, or the like materialin between.

Without desiring to be bound by a particular rationale or theory ofoperation, it is believed that one of the means by which the dressing ofthe present invention promotes wound healing is by passively deliveringsilver ions present in the material 10 or 20 to migrate into the woundand the surrounding skin. The silver ions are formed from the passivedissolution of silver in an ionic form from the metallic silver surface.An electrolyte is not required for release of silver from metallicforms-only a liquid. Silver ions are released from the silver coatedbase fibers by a process called oligodynamic action, i.e., the passivedissolution of silver into a solution. The process was first observed bya Swiss researcher in the 1890's , viz., when metallic silver comes incontact with a water-containing liquid, a small (“oligo-”) amount ofsilver is released into the solution (“dynamic”). Silver is typicallynot released on a completely dry wound absent other conditions. Theforegoing is consistent with the fact that the analgesic effect of adressing in accordance with the present invention is experienced whenapplied to a dry wound but the antibacterial effect is not.

Without wishing to be bound by any particular theory, three mechanismsof action may account for the pain relieving aspects of the dressing ofthe present invention which have been observed and which are documentedbelow. First, the silver creates an antibacterial environment, which inturn diminishes the inflammation caused by the bacteria and subsequentlydiminishes pain. Second, by separating the layers of silver nylon with anon-conducting material, a capacitative field may be established by thecurrent of injury that is present at the wound surface. Third, asdescribed below, the effect of a highly conductive layer has a positiveeffect on the electro-magnetic field environment of the wound to behealed.

In accordance with early testing, the dressing with the fastest painrelieving aspect was the one with alternating layers of 100% silvernylon and a non-conducting layer, creating a laminate that is eightlayers thick with the 100% silver layer against the wound surface. Whenthis dressing is placed against areas of blunt trauma such ascontusions, sprains (stretched ligaments), and strains (torn muscles) italso provided pain relief. Laminates having four and six layers providedpain relief but not as rapidly as the eight layer dressing. The factthat the multi laminate provided pain relief when the skin was intactsuggests that the pain relieving aspect of the dressing is more anelectrical field phenomena, affecting to the alteration in the electricparameters of the skin that accompanies damaged tissue beneath theskin's surface. Later testing discussed below confirms the significanceof the electrical effect of the conductive layers of the presentinvention.

An advantage of the present invention over the prior art is that it doesnot require an external energy source or galvanic cell action to createand deliver silver ions. The laminate form of the present invention canbe utilized to provide a gradient concentration in succeeding layers orwithin a single layer. Interposing non-conductive layers betweenconductive layers establishes a capacitive effect which is thought toincrease the concentration of the silver ions delivered to the bodysurface upon which the dressing is placed. The laminate structure 10 or20 of the present invention can be formed into a number of differentuseful forms, depending on the particular application and by controllingthe permeability of the dressing or by covering the dressing with amembrane of a desired porosity, the proper moisture environment at thetreatment site is created and maintained, which further increases silverion migration.

The present invention exhibits an improved degree of control, comparedto previous systems, over the delivery and targeting of silver, viz., bythe multiple layers and silver concentration gradient features of thepresent invention. The pain relieving characteristics of the dressingare also noted. The pain relieving effect is enhanced by making thesilver containing layers out of 100% silver nylon.

In contrast to antimicrobial creams and emollients which aregas-impermeable, the dressing of the present invention creates a moistenvironment with gas permeability that promotes healing by adding asemiocclusive outer layer. The present invention is easier to replaceandassists in keeping the wound site clean, rather than having to wash,rinse or otherwise traumatize the site to remove old creams or the like.

The invention will be further described in connection with the followingexamples, which are set forth for purposes of illustration only. Partsand percentages appearing in such examples are by weight unlessotherwise stipulated.

EXAMPLES Example 1 Laminate of Alternative Layers of Silver and DelNet®

A dressing material was made of three layers. The layer that was againstthe bacterial culture called “SN” was 100% silver plated nylon woven ina pattern called “warp knit” with individual 15 denier fibers. The nextlayer, “DK2”, was a non-woven 2 oz fabric composed of a mixture of 25%three denier silver plated fibers and 75% three denier rayon fibers. Thethird layer, “DK8”, was a non-woven 8 oz. fabric composed of a mixtureof 5% three denier silver plated fibers and 95% three denier rayonfibers. The layers were laminated by needle punch. The ratio of thesilver to nonmetalized fiber was as follows for each layer:

Layer 1 100% silver nylon Layer 2 25% silver nylon to 75% nonmetalizedfibers Layer 3 5% silver nylon to 95% nonmetalized fibers

The purpose of this Example is to determine the effectiveness of SilverNylon Fabric Type “SNDK2DK8” with Antimicrobial Disk SusceptibilityTesting against four primary organisms that contribute to an infectiousprocess warranting antimicrobial treatment.

The Kirby-Bauer Standard Antimicrobial Suseptibility Test showed thatthe multilayer SNDK2DK8 was an effective antimicrobial agent forinhibiting bacterial growth. In this test, multilayer SNDK2DK8, controlwithout silver fibers and DK100 (nonwoven single layer 100% silverplated nylon fibers) was tested in broth cultures of selected organisms.The broth is inoculated onto the surface of a Mueller-Hinton agar platein three different directions. The test sample is then centered on theagar surface and incubated at 35-37° C. for 16 to 18 hours. Afterincubation, the diameter of the growth free one of complete inhibitionincluding the diameter of the disc is measured to the nearest wholemillimeter. The resultant zone of the inhibition is a qualitativeindication of antimicrobial activity.

The following organisms were tested:

-   Escherichia coli ATCC:25922-   Pseudomonas aeruginosa ATCC:27853-   Enterococcus faecalis ATCC:29212-   Staphylococcus aureus ATCC:29213

After the 72 hr. reading, the “SNDK2DK8”, DK100 and Control discs wereremoved with sterile tweezers and moved to a different area of growth onthe plate. The plates were placed back into the incubator and reexaminedafter 144 hrs. The control discs showed no growth inhibition while theSNDK2DK8 showed the greatest inhibition followed by DK100. The E. coli.,E. faecalis, and S. aureus plates exhibited no sign of diminished zonesof inhibition after the SNDK2DK8 and DK100 disks were removed from theoriginal site. There were no new zones observed around the SNDK2SK8 andDK100disks when placed in the new area of the plate. However, on the P.aeruginosa plates the zones of inhibition increased from 12 mm to 24 mmin the areas where the disks were removed and new zones of inhibitionwere formed around the disks after they were moved to a new area of theplate measuring 10 mm/72 hrs.

FIGS. 9-12 are graphs of the foregoing testing.

Clinical Examples

Clinical Case No. 1

FD is a 5 year old female who suffered partial thickness burns to thedorsal aspect of here right foot as a result of excessive sun exposure(sunburn). Antibiotic cream was applied that evening by the parents.Within 24 hours multi laminate silver dressings of the present inventionwere applied. The patient noted relief of the pain from the partialthickness burn within 30 minutes and slept the entire night pain free.The partial thickness burn healed within twenty four hours. No tattooingor scarring was present.

Clinical Case No. 2

RF is a 41 year old female who suffered partial thickness burns to thevolar aspect of her forearm as a result of spilling boiling water on herforearm. The patient was seen in a local emergency room, silvadene creamwas applied and analgesics prescribed. Within 48 hours, a multi laminatesilver dressing in accordance with the present invention was applied.The patient note relief of the pain of the burn within four hours anddid not require any analgesics. She returned to the clinic in three daysat which point the wound was completely healed. And the dressings werediscontinued. The partial thickness burn healed within 48 hours.

Clinical Case No. 3

LS is a 44 year old female who suffered a postoperative wound infectionand soft tissue breakdown in the popliteal fossa (back of knee). The daythe dressings were initiated was noted in photograph No. LS-1 (See FIG.19). Photograph No. LS-2 (See FIG. 20) was taken twelve days later withdaily dressing changes. The patient noted that within forty-eight hoursthe wound was essentially pain free with the exception when the dressingwas changed and the wound was uncovered. Photograph Nos. LS-3, LS-4 andLS-5 (FIGS. 21-23) show progressive wound healing. Photograph No. LS-6(FIG. 24) shows the wound healed.

Clinical Case No. 4

JL is a 46 year old female who suffered a sharp laceration to the radialaspect of her index finger. Soft tissue was lost that extended down tothe tendon (Photograph No. JL-1) (See FIG. 25). Dressings were changedon a daily basis. Photograph Nos. JL-2 and JL-3 (see FIGS. 26 and 27)show progressive wound healing. The patient noted that the wound waspain free after 48 hours. At the completion of wound healing (PhotographNos. JL-4 and JLS) (See FIGS. 28 and 29), the patient noted full rangeof motion of the digit with normal sensation to light touch.

The results of the foregoing Examples show that the multilayer laminateof the present invention clearly provides significantly improvedbenefits over a single layer dressing. While prior dressings may haveincorporated more than one layer, they only contemplate the use of asingle layer of silver-coated fibers. An unexpected result of thepresent invention is that multiple layers of silver, particularly wherethe layers are separated by nonconductive layers of material, provideimproved silver ion migration and improved healing, antibacterial andantifungal properties.

The above described laminate structures, i.e., laminates of successivelayers containing different ratios of metalized fibers to non-metalfibers and laminates with alternating layers of conductive andnon-conductive fibers result in enhanced wound healing as well asprovide an analgesic effect. The inventor has discovered that creating alaminate of one or more plies of a highly conductive metal or metalcoated fabric has shown to be highly effective demonstrating apronounced analgesic and wound healing effect on biological tissues evenabsent alternating nonconductive layers. The inventor has discoveredthat the passive conductivity of a highly conductive dressing is a keyfactor in promoting healing of biological tissues. The greater theconductivity of at least one layer of the laminate the greater theanalgesic effect reported on injured tissue. The analgesic effect ismost pronounced on acute injuries but is also present on chroniclesions. With highly conductive dressings in accordance with the presentinvention, metal ion flow is not required to produce the analgesicproperties of the appliance and improve tissue healing characteristics.The dressing can even be placed several millimeters above the wound andstill exhibit analgesic and healing effects. Ion flow is, however,³required for the antimicrobial effect.

This second type or class of dressing appliance described below istypified most completely by a highly conductive material that whenplaced on the wound surface or on the skin overlying the areas of softtissue or osseous injury, assists with the healing of the involvedtissues and provides an analgesic effect. The dressing affects theelectrical potentials in and around the tissue injury site. Theelectrical parameters promoting healing and analgesic are reestablishedpassively. The effectiveness of the embodiment rests with the maximizingof conductivity and minimizing of resistance of the dressing.

FIG. 30 is a cross sectional representation of typical mammalian skin 5with an electrical circuit generated by the TEP overlayed on theanatomy. The epidermis 7 overlies the dermis 9 at junction 11 andincludes the stratum corneum layer 13 and the stratum spinosum layer 15with junction 17 therebetween. The stratum corneum layer is composed ofdead cornified squamous epithelium. The space 19 represents a wound thatis filled with both cellular and dissolved elements of the bloodincluding fibrinogen, fibronectin, polymorphonuclear leukocytes,platlets and red blood cells. The surface 21 of the skin distal to thewound 19 can be expected to have a potential in a range of from −10 to−70 milivolts (depending on the location on the body) due to the TEP.The potential on the surface of the wound is designated by reference no.23. The resistance of the return paths of the current induced by theepidermal battery is represented by resistors 25. The resistance of thewound is represented at 27. The epidermal battery is represented bysymbols 29. A dressing 110 in accordance with the present invention andhaving highly conductive layer 114, absorbent layer 116, semipermeablelayer 118 and tape layer 112 is shown proximate the wounded skin surface21. Prior to placement of dressing 110 on the wound 19, the woundpotential, e.g., at 23, is more positive than on the surface of theskin, e.g., at 21. That is, the surface potential becomes less negativeand can in certain instances become positive. This is due to the removalof the epidermal battery 29 at the wound 19. The further potential testpoint 23 is from the unwounded surface 21, the more closely thepotential at 23 will approximate the potential of the positive side ofthe battery 29. If the wound 19 is wet and therefore conductive, acurrent between points 31 and 33 will be induced by the TEP, i.e., thewound current. The wound current will pass through the exudate fillingthe wound 19 along the most efficient (lowest resistance) pathavailable, most likely proximate the edge of the wound, as this will bethe shortest path and the most moist path. The resistance to the woundcurrent is represented by resistance 27. The wound current will passfrom point 31 through the resistance at the junction 11 represented byresistor 35 into the wound at point 37 through the wound resistance 27to point 39 where it reenters the epidermis 7 at the junction 17 throughthe resistance of junction 17 represented as resistor 25 to point 33 onthe other side of battery 29.

When the dressing 110 is placed on the wound 19, the conductive layer114 lowers the potential of the wound, e.g., at 23 by virtue ofelectrical contact with uninjured skin surfaces at 21 which have anegative potential established by the epidermal battery 29. The dressing110 lowers the potential of the wound surface, e.g., at 23 and providesa conductive bridge between healthy skin surfaces 21 on either side ofthe wound 19. The point of maximum resistance shifts from point 39 topoint 37. This in turn shifts the point of maximum lateral potentialdrop from point 39 to point 37. With the shift in to lateral potential,the electrical characteristics of the wound more closely resemble theamphibian wound than the mammalian wound. It is because of this shiftcaused by the highly conductive surface embodied in dressing 110 thatwound healing is accelerated. The shift in lateral potential alsoreduces the amount of stimulation that superficial nerve endingsreceive, thereby creating the analgesic effect that is noted clinically.It should be appreciated that the moisture retention of dressing 110augments the foregoing process by retaining moisture in the wound tofurther reduce wound resistance 27 and assists with the shift in lateralpotential to deeper structures. Without the present invention,resistance 27 is high, little or no current flows in the wound andlittle or no lateral field exists at the edge of the wound to stimulatehealing.

FIG. 31 is a representative graph of the voltage at the surface of humanskin as one proceeds from normal skin, 21, to the open wound, 23, tonormal skin again. The area of normal skin 21 measures a relativelyconstant negative voltage between 10 and 70 milivolts. The area of thewound surface where the TEP and the epidermal battery is disrupted at 23is always more positive than uninjured skin 21, reaching voltagesbetween 23′ and 23. When a dressing 110 in accordance with the presentinvention is applied and the wound is kept moist, it is possible toreturn to more normal skin potentials as shown at 21′ on the graph. Thepresent invention reestablishes a TEP via a redistribution of surfacepotential.

FIG. 32 reveals the configuration of a standard composite wound dressing110. Layer 114 is a multi-ply or single layer of highly conductivematerial that may be pure metal, combinations of metals, or metal coatedfibers. Layer 116 is an absorbent layer that may be composed of a foamor sponge-like material, such as, cotton, rayon, polyvinyl alcohol,polyvinyl acetate, polyethylene oxide, polyvinyl pyrrolidon,polyurethane hydrocolloids, and alginates. Layer 118 is a semipermeablebreathable urethane barrier film. Layer 112 is an adhesive bandagesimilar to polyester spun-laced apertured non-woven fabric coated on oneside with an acrylic pressure sensitive adhesive.

The conductivity of layer 114 is critical to the invention and isdependent on: (1) the material; and (2) the configuration of thematerial composing the dressing. The key characteristic of the materialcomposing the dressing is the material's conductivity or the number offree electrons that the material can provide. The configuration ofmaterial composing the conductive layer 114 is concerned with: (1) themanner in which the conducting material is coated on to substrates; (2)the geometry of the individual fibers; and (3) the construction of thelayer 114.

Metals are generally recognized as the best conducting materials withthe largest quantity of free electrons. Solid metallic wire-likeembodiments have proven to provide excellent conductivity. Reviewing theproperties of metals as conductors, the volume resistivity values are:

Silver 1.59 × 10⁻⁶ ohm-cm Gold 2.22 × 10⁻⁶ ohm-cm Aluminum 2.65 × 10⁻⁶ohm-cm Nickel 6.03 × 10⁻⁶ ohm-cm Tin 11.0 × 10⁻⁶ ohm-cm Stainless Steel100 × 10⁻⁶ ohm-cm Graphite 1375 × 10⁻⁶ ohm-cm Copper 1678 × 10⁻⁶ ohm-cmConductive Polymers 10,000 × 10⁻⁶ ohm-cm

Other metals such as metallic alloys also have excellent conductivity.Resistivity values vary based upon the relative percentages of eachmetal. The ranges of resistivity are:

Aluminum-Copper 2.74 to 11.2 × 10⁻⁶ ohm-cm Aluminum-Magnesium 3.18 to13.4 × 10⁻⁶ ohm-cm Copper-Gold 2.45 to 14.1 × 10⁻⁶ ohm-cm Copper-Nickel2.85 to 50.1 × 10⁻⁶ ohm-cm Copper-Palladium 2.92 to 6.1 × 10⁻⁶ ohm-cmGold-Palladium 2.86 to 27.6 × 10⁻⁶ ohm-cm Gold-Silver 2.75 to 10.4 ×10⁻⁶ ohm-cm Iron-Nickel 12.0 to 33.9 × 10⁻⁶ ohm-cm Silver-Palladium 3.70to 40.6 × 10⁻⁶ ohm-cm

From the perspective of conductivity, silver is the ideal metal toutilize in layer 114 based upon the fact that it has the lowest volumeresistivity. (The salts of silver as well as the silver complexes, bothorganic and inorganic, are very poor conductors and essentially act asdielectric insulator materials. The prior art utilizing silver andsilver compounds has focused primarily upon the ability of the metallicsurface to provide silver ions rather than electrical conductivity.)Ionic silver has the added benefit of exhibiting significantantimicrobial action with minimal potential for allergic reactions.

Conductive gels, conductive pastes, and elastomers such as rubberlikesilicon in which suspended metal particles are present may be used inlayer 114. Superconductive alloys and compounds would also be excellentto use if the superconductivity were possible at room temperature.

Metallic coated surfaces on elastomeric substrates have been found toprovide excellent conductivity. The metal can be coated onto the basefiber by spraying, vapor deposition, dipping or other techniques knownto those skilled in the art. The technique that provides the greatestconductance and lowest resistance has been shown to be autocatalyticelectroless plating. Suitable elastomeric substrates for use in thepresent invention include but are not limited to: nylon, fiberglass,cotton, silk, polyvinyl alcohol, polyvinyl acetate, polyethylene oxide,polyvinyl pyrrolidone, polyurethane, and rayon. The metal coating formedon a substrate may be applied by vapour deposition techniques such asvacuum evaporation, sputtering, magnetron sputtering, ion plating orautocatalytic chemical electroless plating. To achieve a highconductivity, the metal coating technique of choice is autocatalyticelectroless plating. This process is based on the catalytic reduction ofmetal salts to produce the plated metal in its elemental form. Thisplating technique tends to provide an even coating because the metaldoes not build up on the edges of the sample. Electroless plating coversthe entire surface of the substrate and fills in crevices and sharpcorners, to deposit a coating of equal thickness on the entire sample.The purity of the substrate to be plated is very important in achievinguniformity of metal coating. The higher the purity of the metal coatingthe better the conductivity. The percentage of silver that is plated canvary from 1% to 40% by weight. Before acceptable conductivity isachieved, the percentage of silver should be 10% by weight. The idealplating percentages run between 14% and 20%. Above 20% there is littleimprovement in conductivity with increasing silver content.

The thickness of the metal coating also affects conductivity. Acceptablelevels of conductivity are achieved with coatings greater than 0.2micrometers. The ideal coating thickness is between 0.4 micrometers and1.2 micrometers. As noted, the purity and uniformity of metal coating onelastomeric substrates is best achieved by the autocatalytic electrolessplating process. Electroless silver plating essentially involves themirroring reaction also known as the Tollens Test expressed in thefollowing form:RCHO+2Ag(NH₃)20H→2Ag+RCOO-NH₄++H₂O+3NH₃

Electroless plating baths are designed such that when a catalyzedsubstrate is introduced into the plating bath, deposition of the metalbegins in a slow and even manner. Once the process is initiated, theplating solution will continue to plate because the deposited metalcatalyzes its own its own electroless plating, thus making the reactionautocatalytic.

The conductivity of various materials prepared in accordance with thepresent invention is presented in Table I below. In all cases, theautocatalytic plating process was superior to the vapour depositionprocess, the silver phosphate glass composition, and the silver ion beamprocess in producing highly conductive material. The vapour depositionprocess, the silver phosphate glass composition, and the silver ion beamprocess produce a non-uniform coating of metal on substrate. The vapourdeposition process is the better of the three but still has limitationsdue to the lack of uniformity and continuity of the plating process. Asanticipated, pure metal screening has excellent conductance but lacksthe requisite softness and pliability that would enable it to bepreferred for use in wound dressings. Accordingly, metallized flexiblefibers such as nylon are preferred for such applications. Additionalsuitable fibers are identified in the preceding description of laminateembodiments of the present invention. In addition to the selection offiber and metallic coating, the shape of the fibers (and resultantcoated fibers) and their integration into a layer, e.g., by weaving,knitting, etc., play a large part in the resultant conductivity of thelayer 114.

The various cross-sectional shapes that may be imparted to individualfibers are known to those skilled in the art. Generally recognizedcross-sectional shapes are: round, oval, kidney-bean, dogbone, flat,trilobal, and multilobal. For the purposes of the present invention, thegreater the amount of surface area that is metal plated with a uniformthickness, the greater the conductivity. Fibers with denier size between1 and 80 show excellent conductivity.

Individual fibers may be fabricated into several different types ofyarns: spun yarns; filament yarns; compound yarns; and fancy yarns. Thefilament and compound yarns that exhibit multiple longitudinal filamentsexhibit the greatest conductivity. The greater the continuity of theyarns, the greater the potential for excellent conductivity when plated.

Fibers and/or yams are assembled into fabrics: woven fabrics, twistedand knotted fabrics, knit fabrics, nonwoven fabrics, andcompound/complex fabrics. The inventor has found that the total surfacearea of the fibers that compose the fabric is an important variable indetermining conductivity. The manner in which the fibers interact andtouch each other also influences conductivity. The present inventionrecognizes that a plurality of metallized fabric plies can be stackedand/or joined together to decrease the resistance of the compositemulti-ply conductive layer 114. The resistance per unit surface area(one to four plies) of representative samples of the major fabriccategories is summarized in Table 1 below. In the knitted fabric line,utilizing the autocatalytic silver plating technique, double rib knitwith central pile, tricot jersey knit, warp knit, and tricot warp knitwere evaluated. In all cases, as the thickness of the layer increased,the resistance decreased per unit area. The knit fabrics that could bestretched (tricot jersey knit, warp knit, and tricot warp knit) noted asmall reduction in resistance when placed under tension. Although allknit products preformed very well, the double rib knit with central pileperformed the best at one ply. The one ply double rib knit containedapproximately the same amount of silver as four plies of the tricotjersey knit. The double ply of this rib knit provided excellentcontinuity and fiber contact.

In the woven fabric line, the rip stop, plain weave, and pile weave allshowed reduction in resistance as plies were added. The pile weaveexhibited excellent conductivity even with one ply. The rip stop hadmore fibers per unit area and therefore greater conductivity.

In the spun bond nonwoven pattern, the conductivity was excellent withprogressive reduction in resistance as more plies are added.

For the purposes of the present invention, the criteria of fabric designlies primarily with the resultant conductivity of the material. Thediscussion below will be focused (as an example, not as a limitation) onthe use of a fiber matrix, but it is to be understood that other plystructures are contemplated as within the scope of the presentinvention. It is preferable that the fabric be medical grade withminimal dermal reactivity or sensitivity as well as non cytotoxic. Theplies can be made of the same material, different materials, or, cancomprise two or more materials.

The fabric can be made of pure conductive material or a base fibercoated or otherwise containing the conductive material. For example, thefabric base material can be made of nylon, polyethylene, polypropyleneor other polymer, fibers of which are formed by meltblown, spunbond,spincasting or other techniques known to those skilled in the art andappropriate for the particular coating material and laid down as a maton a foraminous web. Alternatively, threads or fine extruded wirestrands can be woven into a web structure. Conductive material can beincorporated into the base material during the fiber or the web formingprocess, such as by conforming, bicomponent extrusion, or the like. Apreferred material is silver-coated nylon fiber.

It is preferable that the fabric material in each layer have aresistance of

-   -   Broad Range: 1,000 ohms/in² to 0.0001 ohms/in²;    -   Middle Range: 10 ohms/in² to 0.001 ohms/in²    -   Optimal Range: 0.1 ohms/in² to 0.01 ohms/in².

Resistance decreases with increasing numbers of plies or fibers within alayer. Beyond four plies of conductive fabric, the resistance decreasebecomes nonappreciable from a clinical point of view although theresistance continues to decrease with additional layers. The practicalupper limit of the conductive plies is ten. Also, cost, thickness,composition, fiber density and weave structure and other factors maylimit the number of plies. A denser fabric design may need only one plyto achieve the same resistance measurement as more than one ply of ahighly absorbent, less dense material. This was seen with the pile wovenand the double rib knit reported in Table 1. The key to reducing theresistance of the conductive layer 114 lies primarily in the manner inwhich the fabric is plated and secondarily in how the layer 114 isconstructed. Fabrics where the fibers are continuous or even meltedtogether generally have lower resistance with greater continuity of themetallic layer. The larger the surface area of fiber contact the betterthe conductivity and the lower the resistance.

One means for laminating and electrically integrating the plies is bypoint embossing or point bonding achieved by passing the fabric betweena pair of niprolls, one roll having a series of spaced apart pinsextending radially from the roll, and the other roll being flat. As thefabric plies are passed between the niprolls the pins press into theplies and force the fibers of one ply into the interstices of the nextply, thus bonding the two plies by fiber-to-fiber interaction forces.Alternatively, the plies can be laminated by adhesives, spot bonding (byultrasonic welding or laser welding) or other techniques known to thoseskilled in the art. The optimal technique for laminating the plies issewing them together with conductive thread preferably autocatalyticsilver nylon plated poly or monofilament silver nylon thread. Theconductive laminating thread enhances the overall conductivity of theconductive layer 114 and minimizes the resistance.

The fibers of the nylon fabric enhance continuity of the metal plating,thereby increasing conductivity. When the conductive layer 114 iscomposed of fabrics that can be stretched, the metal plated nylon iswrapped around elastic fibers so as to provide optimal conductivity asthe fabric is stretched.

Other materials can be incorporated into the fabric, such as, but notlimited to, antibiotics, fungicides, topical anesthetics, desiccants orabsorbents, materials designed to wick fluid away from the wound site,materials designed to retain moisture or fluid, microencapsulatedmaterials for prolonged or selective release into the wound area, andthe like.

Clinically, it has been observed that the lower the resistance of theconductive layer 114, the faster the pain relief, the faster the woundhealing and the greater the edema reduction. Accordingly, the presentinvention provides a dressing that stimulates healing of the underlyingtissues and provides an analgesic effect. In order for the dressing 110to provide its beneficial effect over an acceptable period, means mustbe provided to maintain high conductivity that persists over an extendedperiod of time and in the presence of wound exudate, body sweat orbodily fluid discharges. In order to achieve this objective of longduration conductivity, several constructions are presented herein,namely, the conductive layer 114 can be: (1) a multi-ply laminate havinga plurality of plies of conductive material, preferably in electricalcontinuity at numerous points of contact or (2) a conductive layer 114with multiple intemal conductive fibers that provides the sameconductivity as the multi-ply laminate. As noted, the conductive layer114 may be part of a multilaminate wound dressing that includes some orall of the following layers: (1) Conductive layer; (2) Absorbent layer;(3) Vapour and non-strick through layer; (4) tape or adhesive layer. Theconductive layer may be positioned against the wound surface or isolatedfrom the wound surface by a semipermeable membrane. In addition, two ormore conductive layers may be included in the same dressing. Theconductive layer 114 can also be attached to an orthopaedic brace or anorthopaedic cast. In such applications, it is useful to employ thefollowing laminar structure: (1) Conductive layer; (2) Padding layer;(3) Adhesive layer.

The conductive layer 114 preferably includes a flexible conductivematerial which can be a fabric or mesh, either woven fabrics, knittedfabrics, twisted and knotted fabrics, nonwoven fabrics, orcompound/complex fabrics, or as long as conductivity is maintained. Forbraces and splints the conductive layer 114 need not be flexible and maybe rigid, semi rigid, or flexible.

The multilayer laminate 110 or the conductive layer 114 alone can bemanufactured into a number of wound dressing products, such as, bandagestrips, wraps, pads, butterfly bandages, multilayer island and stripcomposite wound dressings, external body coverings, near or next to thedermis for blunt trauma or fractures, oral, vaginal, rectal, nasal, earcanal suppositories, napkins and inserts, shoe orthotics, liners forbraces, bra liners, external feminine napkins, catheter tube sleeves,and wound drains.

As noted above, increasing the number of plies in the conductive layer114 improves duration of high conductivity. The multi-plies allow theconductivity to stay high as the dressing stays in contact with thewound. As the ply or plies of dressing closer to the wound increasetheir resistance secondary to the formation of silver chloride crystals,the additional plies electrically contacting these wound contactingplies maintain the conductivity whereas the conductivity of a single plywould be substantially reduced. In a similar vein, multiple pliesmaintain conductivity despite sweat from the dermis containing chlorideions that would otherwise reduce the conductivity of wraps that areplace for closed injuries such as bone fracture, ligament or muscletears, soft tissue contusions.

If a highly conductive layer 114 is employed, alternating nonconductivelayers and gradient of ion concentration features may be eliminatedwhich reduces the cost and bulk of the dressing. While silver is thepreferred coating metal due to its high conductivity, any conductivematerial may be used, expensive silver-containing fabric is thereforenot required.

Tests were preformed on the conductive plies of the conductive layer 114to look for various electrical properties of static and/or dynamicelectrical fields, capacitive effects, inductive effects, andconductivity. The materials did not exhibit any capacitive or inductiveeffects even when placed in stacked plies (but in contact with eachother). With both AC and DC signals applied to these plies, no unusualelectrical characteristics could be found. The only measurable effectwas the conductivity. The fabrics had very low contact resistance, withnon-uniform surface conductivity. The non-uniformity was a function ofthe weave design, the direction of measurement, and the tension appliedto the material.

In order to make accurate and repeatable measurements of the samples, aFabric Holding device was fabricated with a nylon substrate. Brass holddown clamps were precisely spaced with a gap between the plates of 1.00inch. Since similar materials are used on both ends of the fabricclamps, any dissimilar metal effects between the fabric and the clampwould be canceled out. The fabric samples were cut to 1.00 inch widthand 1.25 inch long in both directions of the samples' weave, and placedunder the clamps providing a square inch of exposed material that wastested. The resistance of the sample was measured using a 4 ½ digitmulti-meter (resolution of 0.01 ohms). The basic accuracy of the deviceis +−0.02 ohms. All measurements were corrected for the test leadresistance and meter contact resistance.

The measurements were made with the samples lying flat on the fabricholding device without tension placed on the material. To provide ameasurement under tension, the non-stressed material was elevated (whilemaintaining tightness on the clamps) between the hold-down clamps with awedge that lengthened the 1.00 inch gap between the clamps to 1.10inches. This 10% elongation was used for the measurements under tension.

Measurements were limited to silver containing plies. The conductivity(units of ohms per square inch) of the autocatalytic plated, vapordeposited plated, ion beam plated, silver salt porcine skin chemicaldeposition and pure metallic silver in foil and sheet form is presentedTable 1.

TABLE I Tricot Jersey Kint Autocatalytic Plated Silver Nylon .9 ouncessilver/m2 Measurement Along 1 Layer 2 Layers: sewn 3 Layers: sewn 4Layers: sewn Warp Direction 0.68 W/in² 0.38 W/in² 0.22 W/in² 0.15 W/in²Weave Direction 0.88 W/in² 0.44 W/in² 0.30 W/in² 0.22 W/in² AlternatingDirection 0.39 W/in² 0.24 W/in² 0.17 W/in² Warp Under Tension 0.51 W/in²Weave Under 0.70 W/in² Tension Measurement Along 1 Layer 2 Layers: glue3 Layers: glue 4 Layers: glue Warp or Weave 0.67 W/in² 0.40 W/in² 0.28W/in² 0.20 W/in² Warp Knit Autocatylitic Plated Silver Nylon 4.0 ouncessilver/m² Measurement Along 1 Layer 2 Layers: sewn 3 Layers: sewn 4Layers: sewn Warp Direction 0.72 W/in² 0.38 W/in² 0.25 W/in² 0.17 W/in²Weave Direction 2.12 W/in² 1.05 W/in² 0.75 W/in² 0.55 W/in² AlternatingDirection 0.55 W/in² 0.45 W/in² 0.30 W/in² Warp Under Tension 0.56 W/in²Weave Under 2.51 W/in² Tension Non-Woven 8 Ounce Autocatylitic PlatedSilvery Nylon Non-Woven 1.05 W/in 1.00 W/in² 0.80 W/in² 0.70 W/in²Double Rib Knit with Central Pile Autocatylitic Plated Silver Nylon 4.0Ounce/m² Warp Direction 0.20 W/in² 0.15 W/in² 0.12 W/in² 0.10 W/in²Weave Direction 0.20 W/in² 0.15 W/in² 0.12 W/in² 0.10 W/in² Spun BondedAutocatylitic Plated Silver Nylon 1.0 Ounce Silver/m² Warp Direction0.38 W/in² 0.30 W/in² 0.27 W/in² 0.20 W/in² Weave Direction 0.38 W/in²0.30 W/in² 0.27 W/in² 0.20 W/in² Conductive Film Polyruethane andAutocatylitic Plated Silver Nylon Staple/fiber Side 1.50 W/in² Rip StopWeave Autocatylitic Plated Silver Nylon 2.2 Ounce Silver/m² Warp 0.30W/in² 0.22 W/in² 0.18 W/in² 0.16 W/in² Weave 0.30 W/in² 0.22 W/in² 0.18W/in² 0.16 W/in² Plain Weave Autocatylitic Plated Silver Nylon 2.2 OunceSilver/m² Warp 0.60 W/in² 0.50 W/in² 0.40 W/in² 0.30 W/in² Weave 0.60W/in² 0.50 W/in² 0.40 W/in² 0.30 W/in² Tricot Warp Knit AutocatyliticPlated Silver Nylon 1.5 Ounce Silver/m² Warp under Tension 0.40 W/in²0.30 W/in² 0.20 W/in² 0.20 W/in² Warp without 0.30 W/in² 0.20 W/in² 0.20W/in² 0.20 W/in² Tension Weave under Tension 0.40 W/in² 0.30 W/in² 0.20W/in² 0.20 W/in² Weave without 0.30 W/in² 0.20 W/in² 0.20 W/in² 0.20W/in² Tension Pile Woven Autocatylitic Plated Silver Nylon 4.0 OunceSilver/m² Warp 0.20 W/in² 0.15 W/in² 0.15 W/in² 0.15 W/in² Weave 0.20W/in² 0.15 W/in² 0.15 W/in² 0.15 W/in² Vapour Deposition Plated ActicoatPlate Side 1.70 W/in² 1.50 W/in² 1.40 W/in² 1.20 W/in² Non-Plated Side2.20 W/in² 2.10 W/in² 1.80 W/in² 1.50 W/in² Silver Phosphate GlassPowder in Adhesive Arglaes^(a) Adhesive Side Infinite Silver Plated IonBeam Technology Spi-Argent^(a) Silver Catheter Infinite Silver LeafPreparation Silver Leaf 0.20 W/in² 0.20 W/in² 0.20 W/in² 0.20 W/in²99.99% Pure Solid Silver Sheet 100 μm thick Silver Sheet 0.18 W/in² 0.18W/in² 0.16 W/in² 0.10 W/in² 99.99% Pure Solid Silver Wire 1/16^(th) inchthick Silver Wire 0.10 W/in² 99.99% Pure Solid Silver Screen with 0.05mm Wires Silver Wire 0.10 W/in² Mediskin I + Silver Procine Skin/Silver50 KW/in² 50 KW/in² 50 KW/in² 50 KW/in² Tricot Jersey Knit AutocatyliticPlated Silver Nylon .9 ounces silver/m² 24 hours soaked in Normal SalineMeasurement 24 1 Layer 2 Layers: sewn 3 Layers: sewn 4 Layers: sewnhours soaked in Normal Saline 3.0 W/in² 1.6 W/in² 1.0 W/in² 0.40 W/in²24 hours on human 30.0 W/in² 15.0 W/in² 8.0 W/in² 2.0 W/in² wound withsilver nylon against the wound surfaceBacteriology and Biological Reaction of Multi-ply Silver ConductiveLayer Dressings

When there is direct contact between the autocatalyitic silver platednylon layer and the wound surface, the oligodynamic action of silver issufficient to provide enough silver ions to act as am antimicrobial. Thefollowing tests were performed to verify this statement.

Test 1: Kirby-Bauer Standard Antimicrobial Suseptibility Test

The Kirby-Bauer Standard Antimicrobial Suseptibility Test showed thatthe multilayer autocatalytic silver plated nylon was an effectiveantimicrobial agent for inhibiting bacterial growth. In this test themultilayer autocatalytic silver plated nylon was tested in brothcultures of selected organisms. The broth is inoculated onto the surfaceof a Mueller-Hinton agar plate in three different directions. The testsample is them centered on the agar surface and incubated at 35-37° C.for 16 to 18 hours. After incubation, the diameter of the growth freezone of complete inhibition including the diameter of the disc ismeasured to the nearest whole millimeter. The resultant zone ofinhibition is a qualitative indication of antimicrobial activity.Studies were preformed by independent NAMSA of Kenesaw, Ga.

Test Organism Results (Zone width-Sample width)/2 S. aureus 2 mminhibition of growth under sample ATCC 33591 S. aureus 2 mm inhibitionof growth under sample ATCC 6538 P. aeruginosa 2 mm inhibition of growthunder sample ATCC 9027 E. faecalis 1 mm inhibition of growth undersample ATCC 51575Test 2: Dow Corning Corporate Test Method 0923 AntimicrobialActivity-Dynamic Test of Surfaces

The Dow Corning Corporate Test Method 0923 AntimicrobialActivity-Dynamic Test of Surfaces is a technique to screen theeffectiveness of an antimicrobial agent applied to the surface of atextile. The method measures the antimicrobial activity of a treatedtextile by shaking a sample in 1.0-2.0×104 CFU/ml of a bacterialsuspension for one hour contact time. The suspension is diluted beforeand after contact to determine bacterial counts. Study was preformed byan independent lab NAMSA of Kenesaw Ga.

TABLE 2 Organism Count (CFU/ml) Test Organism Zero Time One Hour PercentReduction S. Aureus 10,000 <10 99.90 ATCC 6538 P. aeruginosa 27,000 <1099.96 ATCC 9027Test 3: Assessment of Antibacterial Finishes on Textiles Material AATCCTest Method 100 (Modified)

The Assessment of Antibacterial Finishes on Textiles Material AATCC TestMethod 100 (Modified) is a test method that determines whether theantimicrobial surface is effective or bactericidal and is recorded inpercent of bacteria killed. A 4.8 cm disc of multilayer autocatalyticsilver plated nylon is innoculated with 1-2×10⁵ CFU of S. aureus and P.aeruginosa. The percent of bacterial reduction is determined from thecounts taken at zero time and after 24 hours incubation. The study waspreformed by an independent lab NAMSA of Kenesaw Ga.

TABLE 3 Results in CFU/ml Bacterial Zero Contact 24 Hr. Contact SpeciesTime Time Percent Reduction S. aureus 1.4 × 10⁵ <1.0 × 10² 99.93 P. 2.7× 10⁵ <1.0 × 10² 99.97 aeruinosaTest 4: Antimicrobial Effectiveness Test

The object of the antimicrobial effectiveness test is to demonstrate thelevel of effectiveness of the antimicrobial surface. Twenty grams ofautocatalytic plated silver nylon is aseptically placed in 200 cc ofnormal saline and inoculated with the appropriate amount of inoculumsuspension to obtain a population between 10⁵ and 10⁶ CFU/ml. Afterinoculation (day 0), the number of viable microogranisms foreach.organism will be determined by the standard plate count methodusing TSP for plating the bacterial organisms and SDA or PDA for platingfungal organisms. Test preparations are stored at 20° C.-25° C. for aperiod of 28 days. Aliquots from each of the inoculated testpreparations are plated at 7, 14 ,21, and 28 days post inoculation todetermine by standard plate count method using TSA and SDAor PDA.Sterile 0.9% saline or letheen broth will be used as a diluent. Allbacteria plates will be incubated at 30° C. to 35° C. for 3 days; fungalplates are incubated at 20° C. S 25° C. for five days. Study waspreformed by an independent lab NAMSA of Kenesaw Ga.

TABLE 4 Multilaminate Autocatalytic Plated Silver Nylon S. aureus P.aeruginosa E. coli C. albicans A. niger ATCC 9027 ATCC 8739 ATCC 6538ATCC 10231 ATCC 16404 Count of 2.9 × 10⁷ 3.7 × 10⁷ 5.1 × 10⁷ 9.5 × 10⁷2.4 × 10⁷ Inoculum Calculated 1.5 × 10⁵ 1.9 × 10⁵ 2.6 × 10⁵ 4.8 × 10⁵1.2 × 10⁵ Organisms per g of Product Day 0 2.0 × 10³ 2.0 × 10⁴ 2.0 × 10⁵2.1 × 10⁵ 5.0 × 10⁴ Day 7 <10 <10 <10 <10 <10 Day 14 0 0 0 0 Day 21 0 00 0 0 Day 28 0 0 0 0 0

The result of Test 4 clearly shows that the multilaminate autocatalyticplated silver nylon is extremely effective as an antimicrobial surfacein providing a sustained release of silver for antimicrobial activity.Study was performed by independent lab NAMSA of Kenesaw, Ga.

Test 5: ISO Sensitization Study in the Guinea Pig

In order to demonstrate that the autocatylitic silver plated nylonconductive layer 114 does not react adversely with the skin orsurrounding body environment, a guinea pig maximization test of themultilaminate autocatalytic plated silver nylon was performed to lookfor delayed dermal contact sensitization. The multilaminateautocatalytic plated silver nylon was extracted in 0.9% sodium chlorideUSP (SC) and cottonseed oil, NF (CSO). Each extract was intradermallyinjected and occlusively patched to ten test guinea pigs (per extract)in an attempt to induce sensitization. The vehicle was similarlyinjected and osslusively patched to five control guinea pigs (pervehicle). Following a recovery period, the test and control animalsreceived a challenge patch of the appropriate test article extract andthe reagent control. In addition the test article was applied to thesame animal. All sites were scored at 24, 48, and 72 hours after patchremoval. Under these conditions, the SC and CSO test article extractsand the test article showed no evidence of dermal contact sensitizationin the guinea pig. Study was performed by independent lab NAMSA ofKenesaw, Ga.

Chemical Analysis of the Autocatalytic Plated Silver Nylon

The autocatalytic plated silver nylon layer 114 was subjected to thefollowing tests:

-   (1) Electron microscopy: reveals a uniform circumferential coating    between 0.8 μm and 1.0 μm thick.-   (2) X-ray Diffraction Spectrometry (XRD): reveals the composition of    the coating to be 99% pure metallic silver and 1 % silver oxide;-   (3) Thermal gravimetric analysis of the silver plated surface:    reveals no chemical residues from the plating process with only pure    metallic silver.

Having set forth some of the testing results of the conductive layer114, additional embodiments of the present invention shall be describedin conjunction with FIGS. 32-47.

FIG. 33 shows a dressing 120 having the same laminar composition as thedressing 110 shown in FIG. 32 with the exception of the addition ofhighly conductive layer 129 that may be pure metal, combinations ofmetals, or metal coated fibers similar to layer 124 or 114. Dressing 120also includes absorbent layer 126 and semi-permeable layer 128.

The dressing 130 of FIG. 34 is appropriate for application to a brace,splint or orthopaedic appliance and includes adhesive bandage 132,conductive layer 134 and semipermeable layer 138. Layer 132 is optionaldepending on the manner in which the dressing is affixed to theorthopaedic device.

FIG. 35 shows a multilayer dressing/appliance 140 with two layers ofconductive material, 144, separated by a layer of absorbent material,146. The preferred absorbent material is a urathane foam. The specificapplication of dressing 140 is described below in reference to FIGS. 7and 8.

FIG. 36 shows the multilaminate material of FIG. 35 formed into theshape of a packing 150 for body cavities, e.g., nasal, auditory canal,vagina. As noted in reference to FIG. 35, the packing 150 has anabsorbent layer 156 sandwiched between two conductive layers 154. Astring 157 is provided to assist removal of the packing 150.

FIG. 37 shows a cavity packing 160 having a flexible, porous, outer sack161 which contains a multitude of small cubes or chunks 163 of thetn-layer material 140 shown in FIG. 35. A pliable sack 161 allows thechunks 163 to conform to irregular cavities. A string 167 is providedfor removal of the packing 160 and may also be employed as a cinch toclose sack 161.

FIG. 38 shows a covering 170 for one of more teeth formed from themultilayer material 140 shown in FIG. 35. Preferably, the absorbentmaterial selected has elastic memory to conform to the dimensions of thetooth and gum. Alternatively, the conductive layers 174 and theabsorbent layer 176 may be selected to yield a deformable dressing thatwill take a set, e.g., when pressed into contact with the tooth and gumby a dentist.

FIG. 39 shows a tube 180 fabricated from material 140. The tube may beprovided with elastic memory for use in surrounding generallycylindrical objects.

FIG. 40 shows a multi-ply silver nylon conductive layer 184 placedagainst the gingival tissue on the buccal surface. This dressing may beheld in place by insertion between the lip and gum, by wiring oradhesives.

FIG. 41 shows schematically how four plies of silver nylon 194 a-194 dmay be woven together to form a unitary multi-ply conductive layer 194.

FIG. 42 shows a glove 200 formed from the material 190 shown in FIG. 41.The conductive layer 194 of the present invention can be used forhealing and analgesia of osteoarthritis.

FIG. 43 shows a wound drain 210 that is a multi-ply tube made fromsilver nylon. Any number of conductive layers may be employed, i.e., inconcentric cylinders, which may be interleaved with absorbent layers.

FIG. 44 shows a foot orthotic 220 with a layer of foam 223 and a layerof highly conductive silver nylon 224. Alternatively, the foam layer 223could be positioned on the bottom and the conductive layer 224 on top.As a further alternative, the conductive layer 224 may be sandwichedbetween two layers of foam 223.

FIG. 45 shows a knee sleeve 230 formed from at least one conductivelayer 194, e.g., as shown in FIG. 41.

Clinical Findings

Clinical Data

Clinical evaluation of the analgesic effect of the dressing wasconducted utilizing a visual analogue scale (VAS). (see MethodologicalProblems in the Measurement of Pain:A comparison between the verbalrating scale and the Visual Analogue Scale, Ohnhaus, E. E., and Adler,R., Pain 1 (1975), Page: 379-384 Elsevier/North-Holland, Amsterdam). Thevisual analogue scales are useful for measuring pain relief; the valuescorrelate well with those for measuring pain intensity. (See Studieswith Different Types of Visual Analogue Scales for Measurement of Pain,Sriwatanakui K, et ali., Clin. Pharmacol. Ther., August 1983 page234-239). The patients were instructed to mark along a linear scale 10cm long according to their interpretation of the pain intensity(Enclosure 1). New VAS sheets were presented to the patient at each offour evaluation points. The far left at the start of the line was nopain and the far right was agonizing pain (pain as bad as it could be)with the inbetween positions on the line progressing from little to mildto moderate to severe. The lines were measured and rounded to thenearest cm. So that the patients would act as their own controls, fourreadings were taken. The first reading was the level of pain onpresentation to the physician with the medical problem untreated. A fourply laminate dressing in accordance with the present invention wasapplied and a VAS was noted at approximately 30 minutes. The dressingwas then removed and a standard non-conductive dressing applied for tenminutes and the VAS recorded. The non-conductive dressing was thanremoved and the four ply laminate dressing was reapplied. After 30minutes the patient marked the final VAS. The four VAS data points iscalled protocol 1.

The clinical cases reported cover a wide spectrum of pathologic states,including bone fractures, soft tissue contusions, ligament sprains,muscle strains, 2 week post surgical incision pain syndrome, and avariety of acute dermal lesions. In all cases, the four layer laminatedressing significantly reduced the patients perception of pain.

Case Studies

Open Acute Laceration

A 34 year old male presented with an acute laceration on the distalphalanx of his middle finger. The laceration was caused by a piece ofsheet metal and extended across the tip of the digit to the tuft of thedistal phalanx, measuring approximately 2 cm in length. The lacerationwas sharp with little soft tissue loss. The wound was inspectedcarefully and a four layer silver dressing applied in the office.Protocol 1 was initiated and findings recorded in Table 5. The patientwas not placed on antibiotics. The four ply silver dressing was left inplace for four days and than changed.

When the patient returned to the clinic in a week, the wound was healedwithout evidence of infection or nerve damage. The patient noted that aslong as he kept the four ply silver dressing in place he had very littlepain.

Acute Open Abrasion

A 52 year old male suffered a partial thickness abrasion to the anterioraspect of his knee after slipping on a cement sidewalk. The abrasion waspartial thickness measuring approximately six cm in diameter. The fourply silver dressing was applied in the office. Protocol 1 was initiatedand findings recorded in Table 5. The four ply silver dressing was leftin place for three days, after which time a dressing was not required.When the patient returned to the clinic in a week, the wound was healedwithout evidence of infection. The patient noted that as long as he keptthe four ply silver dressing in place he had very little pain.

Partial Thickness Burn

A five year old female suffered a partial thickness burn as a result ofover exposure to sunlight on the dorsal aspects of her feet bilaterally.At the time the patient was seen, the dorsal aspect of the feet wereedematous and extremely painful to any pressure. The four ply silverdressing was applied. Protocol 1 was initiated and findings recorded inTable 5. The four ply silver dressing was left in place for three days,after which time a dressing was not required. When the patient returnedto the clinic in a week, the wound was healed without evidence of anyskin changes. The patient noted that as long as he kept the four plysilver dressing in place he had very little pain.

Two Weeks After Wound Closed

A 48 year old male presented with a painful scar two weeks after asurgical repair of an inguinal hernia. Upon examination the surgicalscar was well healed. The four ply silver dressing was applied to skinsurrounding the surgical scar. Protocol 1 was initiated and findingsrecorded in Table 5. The four ply silver dressing was left in place forseven days. When the patient returned to the clinic in three weeks, thesurgical scar was pain free.

Ankle Sprain

A 36 year old male presented with an acute ankle sprain of the lateralligamentous complex. X-rays revealed no fractures and on physicalexamination the problem was limited to the lateral ligamentous complex:the anterior inferior tib-fib ligament and the anterior fibulotalarligament. The four ply silver dressing was applied. Protocol 1 wasinitiated and findings recorded in Table 5. The four ply silver dressingwas left in place for fourteen days under a compressive bandage. Whenthe patient returned to the clinic in two weeks, the ecchymosis andtenderness to palpation over the lateral ligamentous complex was absent.At the time the patient had a negative talor tilt test and a negativeanterior draw sign. He had full range of motion of the ankle joint withno discomfort.

Intercostal Muscle Strain

The patient is a 47 year old female who suffered blunt trauma to theanterior lateral thorasic region between the 6th and the 9th ribs midaxillary line. Seven days after the blunt trauma the patient was seen inthe clinic with exquisite tenderness in the mid axillary line betweenthe 6th and 9th ribs. Chest x-ray was negative for fracture or pulmonarycontusion. The four ply silver dressing was applied under a rib belt.Protocol 1 was initiated and findings recorded in Table 5. The four plysilver dressing was left in place for ten days. In two weeks the patientcalled the office to cancel her appointment due to the fact that she waspain free and had no complaints. The patient noted that as long as shekept the four ply silver dressing in place she had very little pain.

Metatarsal Fracture

The patient is a 56 year old male who suffered a fifth metatarsalfracture secondary to a fall. The fracture pattern was a spiral obliquewithout comminution. The injury was closed. The four ply silver dressingwas applied under a compressive dressing and the foot was placed in afracture brace. Protocol 1 was initiated and findings recorded in Table5. The four ply silver dressing was left in place for three weeks,changing the dressing every seven days. By the end of the third week,x-rays revealed excellent callus formation at the fracture site. At thistime the patients stated that he was pain free. The brace and dressingwas discontinued. The patient returned to the clinic in three additionalweeks to report that he was pain free. His physical examination wasnormal without tenderness over the fracture site. He was discharged fromthe inventor's care at that time.

Clinical Case Studies

TABLE 5 30 Min. 10 Min. 30 Min. Initial After After After Final Wound orInjury Pain Application Removal Application Category (1) (2) (3) (4)Post Surgical Wound Open Acute Laceration 8 1 8 1 Open Acute Abrasion 71 6 0 Open Acute Partial 9 1 8 1 Thickness Burn 2 Weeks After Wound 6 06 0 Closed Sprains/Strains Ankle Sprain 8 1 7 1 Intercostal MuscleStrain 6 2 6 1 Contusion Lower Extremity 8 1 7 1 Fracture MetatarsalFracture 7 1 7 1Footnotes

(1) This is the analogue pain scale notation by the patient at the timeof presentation

(2) This is the analogue pain scale notation by the patient thirtyminutes after the dressing was applied.

(3) This is the analogue pain scale notation by the patient ten minutesafter the dressing was removed and replaced by a standard non-conductivewound dressing. The replacement of the dressing was after it had been onthe lesion for 30 minutes.

(4) This is the analogue pain scale notation by the patient thirtyminutes after the standard non-conductive dressing was was removed andthe conductive dressing applied.

Visual Analogue Pain Scale and Instructions

The VAS Scale is simply a horizontal line that is accompanied by thefollowing instructions.

“Place one mark on the line drawn below to indicate the level of painthat you are currently experiencing at this moment. The far left at thestart of the line represents no pain while the far right representsagonizing pain (pain as bad as it could be) with the inbetween positionson the line progressing from little to mild to moderate to severe.”

Although only a few exemplary embodiments of this invention have beendescribed in detail above, those skilled in the art will readilyappreciate that many modification are possible in the exemplaryembodiments without materially departing from the novel teachings andadvantages of this invention. Accordingly, all such modifications areintended to be included within the scope of this invention as defined inthe following claims. In the claims, means plus function claims areintended to cover the structures described herein as performing therecited function and not only structural equivalents but also equivalentstructures.

It should further be noted that any patents, application or publicationsreferred to herein are incorporated by reference in their entirety.

1. A medical device, comprising, a fabric comprising a plurality oflayers of fibrous material, wherein a first layer comprises conductivefibers, and a second layer consists of non-conductive fibers, andwherein the plurality of layers is arranged by alternating a first layerand a second layer, wherein a first layer is capable of being placednearest a body site.
 2. The medical device of claim 1, wherein the firstlayer comprises conductive and non-conductive fibers.
 3. The medicaldevice of claim 1, wherein the fabric is semi-permeable.
 4. The medicaldevice of claim 1, wherein the conductive fibers are coated with ametal, a metal alloy, or a combination thereof.
 5. The medical device ofclaim 4, wherein the metal is silver, gold, aluminum, nickel, tin,stainless steel, copper, or combinations thereof, and the metal alloy isaluminum-copper, aluminum-magnesium, copper-gold, copper-nickel,copper-palladium, gold-palladium, gold-silver, iron-nickel andsilver-palladium, or combinations thereof.
 6. The medical device ofclaim 5, wherein the medical device is shaped for a use around externalfixture pin structures.
 7. The medical device of claim 5, wherein themedical device is shaped for a use around ostomy sites.
 8. The medicaldevice of claim 5, wherein the medical device is shaped for a use aroundtracheostomy sites.
 9. The medical device of claim 5, wherein themedical device is shaped for a use around catheter sites.
 10. Themedical device of claim 5, wherein the medical device is shaped forpacking body cavities.
 11. The medical device of claim 1, wherein thenon-conductive fibers comprise polymers, carbon composites, elastomers,or silicon matrix containing metal particles, or a combination thereof.12. The medical device of claim 1, wherein the non-conductive fiberscomprise nylons.
 13. The medical device of claim 1, wherein the medicaldevice is a wounddressing.
 14. The medical device of claim 1, whereinthe medical device is an orthotic appliance.
 15. The medical device ofclaim 1, wherein the medical device is a dental appliance.
 16. Themedical device of claim 1, wherein the medical device comprises atubular shape.
 17. The medical device of claim 1, wherein the medicaldevice is a wound drain.
 18. A medical device, comprising, a fabricincorporated into an appliance; wherein the fabric comprises a pluralityof layers of fibrous material wherein a first layer comprises conductivefibers, and a second layer consists of non-conductive fibers, andwherein the plurality of layers is arranged by alternating a first layerand a second layer, wherein a first layer is capable of being placednearest a body site.
 19. A method for treating pain and acceleratinghealing comprising, applying a medical device comprising a fabriccomprising a plurality of layers of fibrous material, wherein a firstlayer comprises conductive fibers, and a second layer consists ofnon-conductive fibers, and wherein the plurality of layers is arrangedby alternating a first layer and a second layer, wherein a first layeris in a position adjacent to a surface of a portion of a body of aliving organism.